WO2022176202A1 - Dispositif d'alimentation électrique et système d'ablation - Google Patents

Dispositif d'alimentation électrique et système d'ablation Download PDF

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Publication number
WO2022176202A1
WO2022176202A1 PCT/JP2021/006669 JP2021006669W WO2022176202A1 WO 2022176202 A1 WO2022176202 A1 WO 2022176202A1 JP 2021006669 W JP2021006669 W JP 2021006669W WO 2022176202 A1 WO2022176202 A1 WO 2022176202A1
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Prior art keywords
ablation
electrodes
power supply
catheter
supply device
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PCT/JP2021/006669
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English (en)
Japanese (ja)
Inventor
誠 加藤
卓也 平尾
久生 宮本
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日本ライフライン株式会社
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Application filed by 日本ライフライン株式会社 filed Critical 日本ライフライン株式会社
Priority to PCT/JP2021/006669 priority Critical patent/WO2022176202A1/fr
Priority to DE112021007139.4T priority patent/DE112021007139T5/de
Priority to US18/252,576 priority patent/US20240016536A1/en
Priority to CN202180073749.7A priority patent/CN116456920A/zh
Priority to JP2023500493A priority patent/JPWO2022176202A1/ja
Priority to TW111102737A priority patent/TW202233133A/zh
Publication of WO2022176202A1 publication Critical patent/WO2022176202A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/1206—Generators therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/1206—Generators therefor
    • A61B18/1233—Generators therefor with circuits for assuring patient safety
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00053—Mechanical features of the instrument of device
    • A61B2018/0016—Energy applicators arranged in a two- or three dimensional array
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00053—Mechanical features of the instrument of device
    • A61B2018/00214—Expandable means emitting energy, e.g. by elements carried thereon
    • A61B2018/00267—Expandable means emitting energy, e.g. by elements carried thereon having a basket shaped structure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00345—Vascular system
    • A61B2018/00351—Heart
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00577—Ablation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00613—Irreversible electroporation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00696—Controlled or regulated parameters
    • A61B2018/00761—Duration
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00696—Controlled or regulated parameters
    • A61B2018/00767—Voltage
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/1206—Generators therefor
    • A61B2018/124—Generators therefor switching the output to different electrodes, e.g. sequentially
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B18/16—Indifferent or passive electrodes for grounding
    • A61B2018/167—Passive electrodes capacitively coupled to the skin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/327—Applying electric currents by contact electrodes alternating or intermittent currents for enhancing the absorption properties of tissue, e.g. by electroporation

Definitions

  • the present invention relates to an ablation system including an ablation catheter for performing ablation and a power supply device for supplying power for performing ablation, and a power supply device applied to such an ablation system.
  • An ablation system that ablates such an affected area has been proposed as one of the medical devices for treating an affected area in a patient's body (for example, an affected area having a tumor such as cancer).
  • This ablation system includes an electrode catheter as an ablation catheter and a power supply device that supplies power for performing ablation.
  • Patent Literature 1 discloses an ablation system that performs ablation using irreversible electroporation (IRE).
  • a power supply device includes a power supply unit that supplies power for performing ablation using irreversible electroporation to a plurality of electrodes in an ablation catheter; a control unit that controls the pulse voltage so that the pulse voltage having a plurality of types of positive amplitude values is applied to three or more application electrodes including the plurality of electrodes when performing ablation; is provided.
  • An ablation system includes an ablation catheter having a plurality of electrodes, and the power supply device according to one embodiment of the present invention.
  • pulses having a plurality of types of positive amplitude values are applied to the three or more application electrodes.
  • a pulse voltage is controlled such that a voltage is applied.
  • pulse voltage it is generally necessary to apply a very high voltage (pulse voltage) to the electrode. discharge is more likely to occur from If such an electric discharge occurs at the end of the electrode, thrombi may occur during ablation treatment, or the placement position of the ablation catheter may shift due to the impact of the electric discharge.
  • the application of pulse voltages having a plurality of types of positive amplitude values can be easily suppressed, and the application electrodes can be controlled. Since discharge from the end portion is less likely to occur, it becomes easier to prevent the occurrence of thrombi and the deviation of the indwelling position of the ablation catheter as described above.
  • the control unit uses the pulse voltages having the plurality of types of positive amplitude values to determine the absolute value of the difference in the amplitude values of the pulse voltages between the adjacent application electrodes among the three or more application electrodes.
  • the electric field strength near the adjacent application electrodes may be controlled to be equal to or less than a predetermined electric field threshold by controlling to be equal to or less than the first threshold.
  • the electric field concentration is more easily suppressed. Therefore, since the discharge described above is more difficult to occur, the occurrence of thrombi and the displacement of the indwelling position of the ablation catheter as described above can be more easily prevented. As a result, the efficacy of treatment by ablation is further improved.
  • control unit may perform control so that the maximum value of the absolute values of the difference in the amplitude values of the pulse voltages between the adjacent application electrodes is greater than or equal to the second threshold.
  • the absolute value of the amplitude value difference of such pulse voltages is controlled to be equal to or less than the first threshold, and the maximum value of the absolute values of such amplitude value difference is the minimum value. (Second threshold above) or more is secured, so the following is obtained. That is, the above-described electric field concentration is suppressed while ensuring the range in which the electric field is generated (ablation range). As a result, the effectiveness of treatment by ablation is further improved.
  • each of the three or more application electrodes may be composed of three or more electrodes as the plurality of electrodes in the ablation catheter.
  • the application electrode to which the pulse voltage is applied which is the object of control during ablation, is composed only of the electrodes of the ablation catheter (the above three or more electrodes), so the above-described pulse voltage control can be easily done. As a result, convenience during ablation is improved.
  • examples of the above three or more application electrodes include the above-described counter electrode plate and the like, in addition to the electrodes of such an ablation catheter.
  • the ablation catheter includes, for example, a catheter used for treatment of arrhythmia by ablating an affected area in a patient's body.
  • the ablation target may be, for example, an affected area having a tumor in a patient's body.
  • the power supply device and the ablation system when performing ablation using irreversible electroporation, multiple types of positive amplitude values are applied to the three or more application electrodes. Since the pulse voltage is controlled so that the pulse voltage having the voltage is applied, it is as follows. That is, it becomes easier to prevent the occurrence of thrombi and the displacement of the placement position of the ablation catheter as described above. Therefore, it is possible to improve the effectiveness of treatment by ablation.
  • FIG. 1 is a block diagram schematically showing an overall configuration example of an ablation system according to one embodiment of the present invention
  • FIG. FIG. 2 is a schematic diagram showing a detailed configuration example of the ablation catheter shown in FIG. 1
  • FIG. 3 is a schematic diagram showing an example of a deformed state near the distal end of the catheter shaft shown in FIG. 2
  • FIG. 3 is a schematic diagram showing an example of another deformed state in the vicinity of the tip of the catheter shaft shown in FIG. 2
  • FIG. 4 is a timing diagram representing an example of typical voltage waveforms during ablation
  • FIG. 5 is a schematic diagram showing an example of voltage waveforms and the like during ablation according to a comparative example
  • FIG. 4 is a schematic diagram showing an example of voltage waveforms and the like during ablation according to the example.
  • FIG. 8 is a diagram showing an example of magnitude relationships of various parameters shown in FIGS. 6 and 7;
  • FIG. 8 is a diagram showing an example of magnitude relationships of various parameters shown in FIGS.
  • FIG. 1 is a schematic block diagram showing an overall configuration example of an ablation system 5 according to one embodiment of the present invention.
  • This ablation system 5 is a system used for treating an affected area 90 in the body of a patient 9, as shown in FIG. there is
  • the affected area 90 includes, for example, an affected area having an arrhythmia or the like, and an affected area having a tumor such as cancer (liver cancer, lung cancer, breast cancer, kidney cancer, thyroid cancer, etc.).
  • the ablation system 5 of the present embodiment performs non-thermal ablation using irreversible electroporation (IRE) as the ablation of the affected area 90 described above.
  • IRE irreversible electroporation
  • Such an ablation system 5 comprises an ablation catheter 1, a liquid supply device 2 and a power supply device 3, as shown in FIG.
  • the counter electrode plate 4 shown in FIG. 1 is also appropriately used.
  • the ablation catheter 1 is, for example, an electrode catheter that is inserted into the body of a patient 9 through a blood vessel to ablate an affected area 90 to treat arrhythmia, a tumor, or the like.
  • the ablation catheter 1 also has an irrigation mechanism for flowing (injecting) a predetermined irrigation liquid L (for example, physiological saline) from the tip side during such ablation.
  • a predetermined irrigation liquid L for example, physiological saline
  • the ablation system 5 is an ablation system with such an irrigation mechanism.
  • a liquid L is supplied from a liquid supply device 2, which will be described later, so as to circulate and flow (see FIG. 1).
  • FIG. 2 schematically shows a detailed configuration example of the ablation catheter 1.
  • the ablation catheter 1 includes a catheter shaft 11 (catheter tube) as a catheter body (long portion) and a handle 12 attached to the proximal end of the catheter shaft 11 .
  • the catheter shaft 11 is made of a tubular structure (hollow tubular member) having flexibility, and has a shape extending along its own axial direction (Z-axis direction) (see FIG. 2). Specifically, the axial length of the catheter shaft 11 is about several times to several tens of times longer than the axial length (Z-axis direction) of the handle 12 .
  • the catheter shaft 11 has a distal end (flexible distal end portion 11A) configured to be relatively flexible. Further, as shown in FIG. 1, a predetermined tip vicinity structure 6, which will be described later, is provided in the tip flexible portion 11A.
  • This catheter shaft 11 also has a so-called multi-lumen structure in which a plurality of lumens (inner holes, pores, through-holes) are formed inside so as to extend along its own axial direction (Z-axis direction). is doing.
  • Various fine wires (lead wires 50, deflection wires, deformation wires 60, etc., which will be described later) are inserted through the lumen of the catheter shaft 11 while being electrically insulated from each other.
  • a lumen for flowing the above-described irrigation liquid L is formed so as to extend along the axial direction. It is
  • the outer diameter of such a catheter shaft 11 is, for example, approximately 0.3 to 4.0 mm, and the axial length of the catheter shaft 11 is, for example, approximately 300 to 1500 mm.
  • Materials constituting the catheter shaft 11 include, for example, thermoplastic resins such as polyamide, polyether polyamide, polyurethane, polyether block amide (PEBAX) (registered trademark), and nylon.
  • the tip vicinity structure 6 described above includes the branch point of the catheter shaft 11 (located on the proximal end side of the tip vicinity structure 6) and the vicinity of the distal end of the catheter shaft 11 (the tip end described later). a confluence located near the chip 110) and a plurality of (five in this example) branch structures 61a to 61e that are portions that individually connect these branch points and confluence in a curved shape. I'm in. These branch structures 61a to 61e are spaced apart from each other at approximately equal intervals in a plane (XY plane) perpendicular to the axial direction (Z-axis direction) of the catheter shaft 11. As shown in FIG.
  • these branch structures 61a to 61e have one or more electrodes 111 (four electrodes 111 in this example) along their curved extending directions. They are spaced apart from each other at predetermined intervals. Each electrode 111 is a ring-shaped electrode.
  • a distal tip 110 is arranged at the confluence of the branch structures 61a to 61e (near the distal end of the catheter shaft 11).
  • Each of these electrodes 111 is, for example, an electrode for potential measurement or ablation, as described above, and examples thereof include aluminum (Al), copper (Cu), SUS, gold (Au), platinum (Pt), is made of a metal material with good electrical conductivity.
  • the tip 110 is made of, for example, the same metal material as the electrodes 111, and is also made of a resin material such as silicone rubber resin or polyurethane. Examples of parameters of each electrode 111 suitable for ablation using the above-described irreversible electroporation method include the following.
  • each electrode 111 is about 0.3 to 5.0 mm, and the distance between adjacent electrodes 111 along the axial direction of the catheter shaft 11 is is preferably about 0.3 to 5.0 mm.
  • each electrode 111 the tip side of the conducting wire 50 described above is electrically connected individually.
  • the base end side of each lead wire 50 can be connected to the outside of the ablation catheter 1 through the inside of the catheter shaft 11 and the inside of the handle 12 .
  • the base end side of each conductor 50 is taken out from the base end portion (connector portion) of the handle 12 along the Z-axis direction. .
  • the four electrodes 111 arranged for each of the branch structures 61a to 61e described above correspond to specific examples of "three or more electrodes” and “three or more application electrodes” in the present invention.
  • such a shape of the tip vicinity structure 6 is configured to change (deform) according to a deformation operation to be described later on the handle 12 (an operation to the deformation operation section 123 to be described later).
  • a non-deployed shape in which the structure 6 near the tip is not expanded along the axial direction (Z-axis direction)
  • the shape of the tip vicinity structure 6 changes between the expanded shape (expanded shape: see FIG. 2 and FIG. 4 described later) developed along the direction.
  • first shape is a "petal shape” (an example of a flat shape: an example of a flat shape, which is formed by the plurality of branch structures 61a to 61e described above). (See FIG. 3).
  • second shape a shape in which such petal shapes (each branch structure 61a to 61e) are expanded along the axial direction (so-called “basket shape”: FIG. 2 and (See FIG. 4, which will be described later).
  • the above-mentioned “basket shape” means that the shape formed by a plurality of branched structures 61a to 61e, as shown in Figs. , means that they are of similar shape.
  • the handle 12 is a portion that is grasped (grasped) by an operator (doctor) when using the ablation catheter 1 .
  • the handle 12 has a handle body 121 attached to the proximal end side of the catheter shaft 11, a rotation operation section 122, and a deformation operation section 123, as shown in FIG.
  • the handle body 121 corresponds to a portion (gripping portion) that an operator actually grips, and has a shape extending along its axial direction (Z-axis direction).
  • the handle body 121 is made of a synthetic resin such as polycarbonate or acrylonitrile-butadiene-styrene copolymer (ABS).
  • the rotation operation part 122 is a part that is operated during a deflection operation for deflecting (bending) the vicinity of the tip of the catheter shaft 11 (tip flexible part 11A) in both directions.
  • the rotary operation part 122 is used together with a pair of deflection wires (not shown) for such a deflection operation.
  • the operator of the ablation catheter 1 operates (rotates) the rotary operation section 122 .
  • Such a rotary operation unit 122 is configured including a lock mechanism 40 and a rotary plate 41, as shown in FIG.
  • Each tip of the pair of deflection wires described above is fixed to the tip side of the catheter shaft 11 (for example, near the tip 110 described above).
  • Each proximal end of the pair of deflection wires extends from inside the catheter shaft 11 to inside the handle 12 (inside the handle body 121).
  • the rotating plate 41 is a member that is rotatably attached to the handle body 121 about a rotation axis (Y-axis direction) perpendicular to its axial direction (Z-axis direction). be.
  • the rotating plate 41 corresponds to a portion that is actually operated by the operator during the rotating operation described above, and has a substantially disk-like shape. Specifically, in this example, as indicated by arrows d1a and d1b in FIG. ) is possible.
  • the locking mechanism 40 described above is a mechanism for fixing (locking) the rotational position of the rotating plate 41 within the ZY plane.
  • a pair of knobs 41a and 41b are provided integrally with the rotating plate 41 on the side surface of the rotating plate 41, as shown in FIG.
  • the knobs 41a and 41b are arranged point-symmetrically with respect to the rotation axis of the rotary plate 41.
  • Each of these knobs 41a and 41b corresponds to a portion that is operated (pushed) by the fingers of one hand when the operator rotates the rotary plate 41, for example.
  • a rotary plate 41 is made of, for example, the same material (synthetic resin, etc.) as the handle body 121 described above.
  • a pair of fasteners are provided on the rotary plate 41 as described above. These fasteners are members (wire fasteners) for individually fixing the proximal ends of the pair of deflection wires described above by screwing or the like. It should be noted that, with these fasteners, it is possible to arbitrarily adjust the retraction length in the vicinity of each proximal end when fixing each proximal end of the pair of deflection wires described above.
  • the deformation operation section 123 described above is operated by the operator in the deformation operation for changing the shape of the tip vicinity structure 6 between the non-expanded shape (petal shape) and the expanded shape (basket shape). This is the part that is done.
  • the tip side of the deformation wire 60 used in such a deformation operation is fixed to the tip vicinity structure 6 (near the tip tip 110 described above).
  • the proximal end of the deformation wire 60 is taken out from the proximal end of the handle body 121 and attached to the deformation operation portion 123 .
  • Such a deformation operation section 123 is operated along the extending direction (Z-axis direction) of the deformation wire 60, as indicated by arrows d3a and d3b in FIG. ing. As a result, an operation of pushing the deformation wire 60 into the handle body 121 and an operation of pulling out the deformation wire 60 from the handle body 121 are performed.
  • such operations in the directions of arrows d3a and d3b on the deformation operation section 123 correspond to deformation operations for deforming the tip vicinity structure 6.
  • the shape of the tip vicinity structure 6 during the above-described deformation operation changes from the non-expanded shape (petal shape) described above. It can be set to any intermediate shape between the unfolded shape (basket shape).
  • the liquid supply device 2 is a device that supplies the aforementioned irrigation liquid L to the ablation catheter 1, and has a liquid supply section 21 as shown in FIG.
  • the liquid supply unit 21 supplies the above-described liquid L to the ablation catheter 1 at any time according to control by a control signal CTL2, which will be described later. Further, the supply operation of the liquid L is executed or stopped according to the control by the control signal CTL2 described above.
  • a liquid supply unit 21 includes, for example, a liquid pump, a resin tube, and the like.
  • the power supply device 3 provides electric power Pout ( It supplies a pulse voltage (which will be described later) and controls the supply operation of the liquid L in the liquid supply device 2 .
  • the power supply device 3 has an input section 31, a power supply section 32, a control section 33 and a display section 34 as shown in FIG.
  • the input unit 31 is a part for inputting various setting values and instruction signals (operation signals Sm) for instructing predetermined operations.
  • Such an operation signal Sm is input from the input unit 31 according to the operation of the power supply device 3 by an operator (for example, an engineer).
  • these various setting values may be set in the power supply device 3 in advance, for example, at the time of shipment of the product, instead of being input according to the operation by the operator.
  • the set values input by the input unit 31 are supplied to the control unit 33, which will be described later.
  • Such an input unit 31 is configured using, for example, predetermined dials, buttons, a touch panel, and the like.
  • the power supply unit 32 supplies electric power Pout between the ablation catheter 1 (electrode 111) and the return electrode plate 4 described later in accordance with the control signal CTL1 described later for performing ablation using the above-described irreversible electroporation method. part. Further, although the details will be described later, when performing ablation by supplying such power Pout, a high voltage pulse voltage (voltage Vout) is applied to each electrode 111 of the ablation catheter 1. ing. It should be noted that such a power supply unit 32 is configured using a predetermined power supply circuit (for example, a switching regulator or the like).
  • the control unit 33 is a part that controls the entire power supply device 3 and performs predetermined arithmetic processing, and is configured using a microcomputer or the like, for example. Specifically, the control unit 33 first has a function (power supply control function) of controlling the supply operation of the power Pout in the power supply unit 32 using the control signal CTL1. During the power Pout supply operation, the control unit 33 also controls the above-described pulse voltage (voltage Vout). The control unit 33 also has a function (liquid supply control function) of controlling the supply operation of the liquid L in the liquid supply device 2 (liquid supply unit 21) using the control signal CTL2.
  • Temperature information It measured by the ablation catheter 1 (a temperature sensor such as a thermocouple arranged corresponding to each electrode 111) is also supplied to the control unit 33 at any time (Fig. 1).
  • the control unit 33 is supplied with a measured value of the impedance Z between the electrode 111 of the ablation catheter 1 and the return electrode plate 4 (described later) from the power supply unit 32 at any time (see FIG. 1). ).
  • the display unit 34 is a part (monitor) that displays various types of information and outputs them to the outside. Examples of information to be displayed include various set values input from the input unit 31, various parameters supplied from the control unit 33, temperature information It supplied from the ablation catheter 1, and the like. However, the information to be displayed is not limited to these pieces of information, and other information may be displayed instead or in addition.
  • Such a display unit 34 is configured using displays of various types (for example, a liquid crystal display, a CRT (Cathode Ray Tube) display, an organic EL (Electro Luminescence) display, etc.).
  • the return electrode 4 is used in a state of being attached to the body surface of the patient 9 during ablation, as shown in FIG. 1, for example. Specifically, power Pout is supplied between the ablation catheter 1 (electrode 111) and the counter electrode 4 during ablation using the irreversible electroporation method described above. Further, during such ablation, the impedance Z described above is measured at any time, and the measured impedance Z is supplied from the power supply unit 32 to the control unit 33 in the power supply device 3 ( See Figure 1).
  • the above-described irrigation liquid L is supplied to the ablation catheter 1 during such ablation.
  • the liquid L is supplied into the handle body 121 from the base end side (liquid inlet) of the handle body 121 .
  • the power supply device 3 controls the supply operation of the liquid L in such a liquid supply device 2 using the above-described control signal CTL2.
  • the liquid L flows out (is jetted) from the vicinity of the tip of the ablation catheter 1 (the vicinity of the aforementioned branch point in the structure 6 near the tip) to the outside.
  • the operator grips the handle 12 (handle main body 121) with one hand and operates the knob 41a with the fingers of the one hand to move the rotating plate 41 in the direction of the arrow d1a in FIG. 2 (clockwise).
  • the knob 41a with the fingers of the one hand to move the rotating plate 41 in the direction of the arrow d1a in FIG. 2 (clockwise).
  • the operator can rotate the rotary plate 41 to perform a bidirectional (swing) deflection operation in the catheter shaft 11 .
  • the tip flexible portion 11A of the catheter shaft 11 can be bent while the catheter shaft 11 is inserted into the patient's body.
  • the direction (deflection direction) can be freely set. In this manner, since the ablation catheter 1 is provided with a deflection mechanism for deflecting the tip flexible portion 11A in both directions, the shape of the catheter shaft 11 near its tip (tip flexible portion 11A) can be changed. can be inserted into the patient's 9 body.
  • FIG. 3 shows a deformed state (the above-described petal shape state as an example of the above-described non-deployed shape) in the vicinity of the tip of the catheter shaft 11 (the structure 6 near the tip).
  • An example of is schematically represented.
  • 4 (FIGS. 4A and 4B) show another deformed state (the above-described basket shape as an example of the above-described deployed shape) in the vicinity of the tip of the catheter shaft 11 (the tip-near structure 6). state) is schematically shown.
  • the developed shape (basket shape) shown in FIG. 4 is merely an example, and may be, for example, a shape slightly deflated (distorted) from the shape shown in FIG.
  • the distal tip 110 is pulled proximally, so that each of the branch structures 61a to 61e is contracted proximally. That is, the tip vicinity structure 6 becomes the above-described non-expanded shape (in this example, a shape substantially flattened in the XY plane). Specifically, in this example, as shown in FIG. 3A, the shape of the tip vicinity structure 6 is the above-described petal shape constituted by the branch structures 61a to 61e.
  • the tip vicinity structure 6 has the above-described expanded shape (a shape expanded toward the tip side along the Z-axis direction). Specifically, in this example, as shown in FIG. 4A, the shape of the tip vicinity structure 6 is the above-described basket shape composed of the branch structures 61a to 61e.
  • the tip vicinity structure 6 is deformed according to the deformation operation performed on the deformation operation portion 123 .
  • this irreversible electroporation method is attracting attention because it is a non-thermal ablation method as described above and can reduce damage to surrounding blood vessels and nerves.
  • conventional general ablation methods such as RFA (Radiofrequency Ablation) and cryo (freezing) ablation are ablation using thermal energy, so phrenic nerve paralysis and esophageal fistula It may cause complications such as
  • ablation using irreversible electroporation is PFA (Pulsed electric Field Ablation), which uses non-thermal energy, so there is no risk of causing these complications.
  • the myocardium (threshold of electric field intensity: about 400 [V/cm]) is generally first affected by ablation.
  • the electric field strength during this ablation generally affects the esophagus (threshold electric field strength: about 1750 [V/cm]) and the phrenic nerve (threshold electric field strength: about 3800 [V/cm]). It is set to a small value (for example, about 1000 to 1500 [V/cm]). Therefore, as described above, complications such as phrenic nerve paralysis and esophageal fistula do not occur.
  • FIG. 5 is a timing diagram showing an example of a general voltage waveform during ablation.
  • FIG. 5(A) shows an example of a waveform of a general voltage Vout applied to the electrodes of the ablation catheter during RFA
  • FIG. 4A and 4B respectively show examples of typical voltage Vout waveforms applied to electrodes of an ablation catheter during ablation (PFA as described above).
  • the horizontal axis indicates time t
  • the vertical axis indicates voltage (potential difference from the reference potential shown in the figure).
  • the power supplied during this RFA is, for example, about 25 [W].
  • this RFA has become a thermal ablation technique.
  • this PFA is a non-thermal ablation method, unlike the RFA described above.
  • electroporation is generated by applying such a high-voltage short-time pulse voltage to electrodes. Specifically, such pulse voltages create nanoscale holes in the cells to be ablated, inducing apoptosis (cell suicide) in the perforated cells, thereby causing cell death.
  • FIG. 6 schematically shows an example of voltage waveforms during ablation according to a comparative example
  • FIG. 7 shows an example of voltage waveforms during ablation according to an example of the present embodiment. This is a schematic representation.
  • FIG. 8 shows an example of magnitude relationships of various parameters (amplitude value difference ⁇ V and threshold values ⁇ Vth1 and ⁇ Vth2, which will be described later) shown in FIGS.
  • FIGS. 6(E) and 7(E) in the vicinity of the four electrodes 111 (applied electrodes: for convenience, referred to as electrodes 111a to 111d) arranged for each of the branch structures 61a to 61e described above, an example of each equipotential surface Se of the electric field generated with the application of the voltage Vout (pulse voltage).
  • Vout pulse voltage
  • FIGS. 6(A) to 6(D) and FIGS. 7(A) to 7(D) voltages Vout (pulse voltages VoutA to VoutD) individually applied to these electrodes 111a to 111d ) is schematically shown.
  • the horizontal axis indicates time t
  • the vertical axis indicates voltage (potential difference from the reference potential described above). ).
  • pulse voltages VoutA to VoutD having one type of positive (>0) amplitude value Am101 are applied to four applied electrodes (electrodes 111a to 111d). applied separately.
  • the electric field concentration the region where the electric field intensity E is greater than the predetermined electric field threshold value Eth
  • discharge occurs at the inner ends of 111b and 111c.
  • a thrombus may be generated during treatment by ablation, or the impact of the discharge may affect the indwelling position of the ablation catheter 1 (the indwelling position in the body of the patient 9). ) may be misaligned. As a result, in the ablation of this comparative example, the effectiveness of treatment by ablation is reduced.
  • the pulse voltage VoutA 0 [V]
  • the amplitude value Am3 of the pulse voltage VoutB 250[V]
  • the amplitude value Am2 of the pulse voltage VoutC 1250[V]
  • the control section 33 performs the following control using these multiple types of pulse voltages having positive amplitude values. That is, the control unit 33 controls the absolute value of the pulse voltage amplitude difference ⁇ V between the adjacent electrodes 111 among the four electrodes 111a to 111d to be equal to or less than the threshold value ⁇ Vth1 described above. The electric field intensity E in the vicinity of the adjacent electrode 111 is controlled to be equal to or less than the electric field threshold value Eth.
  • the absolute value of the amplitude value difference ⁇ V between the pulse voltages VoutB and VoutC between the adjacent electrodes 111b and 111c is controlled to be equal to or less than the threshold value ⁇ Vth1 ( ⁇ V(BC) ⁇ Vth1).
  • the electric field concentration due to the above-described high-voltage pulse voltage is more easily suppressed than in the comparative example.
  • the electric field strength E at the end near the adjacent electrodes 111b and 111c is equal to or less than the electric field threshold Eth (E ⁇ Eth).
  • the range of absolute values of the amplitude value difference ⁇ V may be set as follows. That is, first, as described above, the absolute value of the amplitude value difference ⁇ V may be set within a range equal to or less than the threshold value ⁇ Vth1 (range R1 shown in FIG. 8: ⁇ V ⁇ Vth1). Further, the control unit 33 may control the maximum absolute value of the amplitude value difference ⁇ V between the pulse voltages of the adjacent electrodes 111 to be equal to or greater than the threshold value ⁇ Vth2 (see FIG. 8). (see range R2 shown in ). For convenience, the range R2 shown in FIG. 8 is shown as ( ⁇ Vth2 ⁇ V ⁇ Vth1). , as described above, is preferably the maximum value among the absolute values of the amplitude difference ⁇ V.
  • thresholds ⁇ Vth1 and ⁇ Vth2 correspond to specific examples of “first threshold” and “second threshold” in the present invention, respectively.
  • a plurality of types of positive amplitude values for example, three types of positive
  • the voltage Vout pulse voltage
  • a pulse voltage for example, pulse voltages VoutA to VoutD
  • amplitude values Am1 to Am3 are applied.
  • the above-described pulse voltages having a plurality of types of positive amplitude values are used, and the absolute value of the amplitude value difference ⁇ V of the pulse voltages between the adjacent application electrodes is set to the threshold value ⁇ Vth1 or less.
  • the electric field intensity E in the vicinity of such adjacent application electrodes is controlled to be equal to or less than a predetermined electric field threshold Eth.
  • the electric field intensity E near the adjacent application electrodes becomes equal to or less than the predetermined electric field threshold, so that the electric field concentration described above can be more easily suppressed. Therefore, since the discharge described above is more difficult to occur, the occurrence of thrombi and the deviation of the indwelling position of the ablation catheter 1 as described above can be more easily prevented. As a result, it is possible to further improve the effectiveness of treatment by ablation using irreversible electroporation.
  • the maximum value of the absolute values of the amplitude value difference ⁇ V of the pulse voltage is controlled to be equal to or greater than the threshold value ⁇ Vth2, the following occurs. That is, while the absolute value of the amplitude value difference ⁇ V of such pulse voltage is controlled to be equal to or less than the threshold value ⁇ Vth1, the maximum value among the absolute values of such amplitude value difference ⁇ V is the minimum value (threshold value ⁇ Vth2). Since the above is ensured, as described above, the above-described electric field concentration is suppressed while ensuring the range in which the electric field is generated (ablation range). As a result, it is possible to further improve the effectiveness of treatment by ablation using irreversible electroporation.
  • all of the above-described three or more application electrodes are configured by the electrodes 111 (three or more electrodes 111) of the ablation catheter 1. Therefore, as follows: Obtain. That is, since the application electrode to which the pulse voltage to be controlled during ablation is applied is composed only of the electrode 111 of the ablation catheter 1, such pulse voltage control can be easily performed. As a result, it is possible to improve convenience during ablation using irreversible electroporation.
  • the materials of the members described in the above embodiments are not limited, and other materials may be used.
  • the configuration of the ablation catheter 1 has been specifically described in the above embodiment, it is not necessary to include all the members, and may further include other members.
  • a leaf spring that can be deformed in the bending direction may be provided inside the catheter shaft 11 as a swinging member.
  • the structure of the handle 12 (the handle body 121 and the rotary operation portion 122) was also specifically described, but it is not necessary to include all the members, and other members may be further included. may be provided.
  • the configuration of the transformation operation unit 123 described above is not limited to that described in the above embodiment, and other configurations may be used.
  • the shape of the vicinity of the distal end of the catheter shaft 11 is not limited to that described in the above embodiment.
  • an ablation catheter of a type (bi-direction type) in which the shape of the vicinity of the distal end of the catheter shaft 11 changes in both directions according to the operation of the rotary plate 41 has been described as an example.
  • the ablation catheter may be of a type (single direction type) in which the shape of the vicinity of the distal end of the catheter shaft 11 changes in one direction according to the operation of the rotating plate 41 . In this case, only one (one) operation wire is provided.
  • the catheter shaft 11 may be an ablation catheter in which the shape of the vicinity of the distal end is fixed. In this case, the operation wire, the rotary plate 41, and the like described above become unnecessary.
  • each electrode 111 in the vicinity of the tip of the catheter shaft 11 is not limited to those described in the above embodiment.
  • the shape of the structure 6 near the tip is not limited to the shape described in the above embodiment (such as the above-described flat shape (petal shape), the above-described non-flat shape (basket shape), etc.), and other shapes.
  • the configuration of the tip vicinity structure 6 itself is not limited to the configuration described in the above embodiment. may be configured.
  • the block configurations of the liquid supply device 2 and the power supply device 3 were specifically described, but it is not necessary to include all the blocks described in the above-described embodiment. Blocks may also be provided. Furthermore, the ablation system 5 as a whole may further include other devices in addition to the devices described in the above embodiments.
  • control operation ablation processing operation using the above-described pulse voltage control, etc.
  • control method ablation method using control of pulse voltage, etc.
  • a method for controlling the pulse voltage is specifically described so that pulse voltages having a plurality of types of positive amplitude values are applied.
  • the pulse voltage is not limited to the method described above, and other methods may be used to control the pulse voltage.
  • the absolute value of the amplitude value difference ⁇ V of the pulse voltage is controlled to be equal to or smaller than the threshold value ⁇ Vth1, or the maximum absolute value of such amplitude value difference ⁇ V is , the threshold value ⁇ Vth2 or more, but may be controlled using another control method.
  • the three or more application electrodes to which the pulse voltage is applied are all configured by the electrode 111 of the ablation catheter 1, but the example in this case is limited. can't That is, for example, in addition to the electrode 111 of such an ablation catheter, three or more application electrodes to which a pulse voltage is applied may be configured, including other electrodes (for example, the counter electrode plate 4 described above). good. Further, in the above embodiment and the like, the case where power Pout for performing ablation using irreversible electroporation is supplied between the plurality of electrodes 111 and the return electrode plate 4 in the ablation catheter 1 is taken as an example. However, it is not limited to this example. That is, as a method of supplying such power Pout to the plurality of electrodes 111, for example, a method of supplying such power Pout between the plurality of electrodes 111 without using the counter electrode plate 4 may be
  • the series of processes described in the above embodiment may be performed by hardware (circuit) or by software (program).
  • the software When it is performed by software, the software consists of a program group for executing each function by a computer.
  • Each program for example, may be installed in the computer in advance and used, or may be installed in the computer from a network or a recording medium and used.
  • the ablation catheter 1 (having an irrigation mechanism) that injects the liquid L for irrigation to the outside has been described as an example, but the present invention is not limited to this example.
  • the present invention may be applied to an ablation catheter that does not have
  • the case where the object of ablation is the affected part 90 having an arrhythmia or the affected part 90 having a tumor in the body of the patient 9 has been described as an example, but it is not limited to these examples. do not have. That is, it is possible to apply the ablation system of the present invention even when the object of ablation is another part (organ, body tissue, etc.) in the patient's 9 body.

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Abstract

Dispositif d'alimentation électrique selon un mode de réalisation de la présente invention comprenant : une unité d'alimentation électrique pour fournir de l'énergie électrique pour effectuer une ablation par électroporation irréversible à une pluralité d'électrodes d'un cathéter d'ablation ; et une unité de commande qui, lorsque l'ablation est réalisée en fournissant la puissance électrique, commande une tension d'impulsion ayant une pluralité de valeurs d'amplitude positive de telle sorte que la tension d'impulsion est appliquée à trois électrodes d'application ou plus comprenant la pluralité d'électrodes.
PCT/JP2021/006669 2021-02-22 2021-02-22 Dispositif d'alimentation électrique et système d'ablation WO2022176202A1 (fr)

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PCT/JP2021/006669 WO2022176202A1 (fr) 2021-02-22 2021-02-22 Dispositif d'alimentation électrique et système d'ablation
DE112021007139.4T DE112021007139T5 (de) 2021-02-22 2021-02-22 Stromversorgungsvorrichtung und Ablationssystem
US18/252,576 US20240016536A1 (en) 2021-02-22 2021-02-22 Power supply device and ablation system
CN202180073749.7A CN116456920A (zh) 2021-02-22 2021-02-22 电源装置以及消融系统
JP2023500493A JPWO2022176202A1 (fr) 2021-02-22 2021-02-22
TW111102737A TW202233133A (zh) 2021-02-22 2022-01-22 電源裝置及消融系統

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Citations (4)

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Publication number Priority date Publication date Assignee Title
JP2010503496A (ja) * 2006-09-14 2010-02-04 ラジュール・テクノロジーズ・エルエルシイ 癌細胞を破壊する装置及び方法
JP2018515247A (ja) * 2015-05-12 2018-06-14 セント・ジュード・メディカル・エイトリアル・フィブリレーション・ディヴィジョン・インコーポレーテッド Ａｃ型心臓不可逆的電気穿孔法のための非対称形にバランスされた波形
WO2020094622A1 (fr) * 2018-11-05 2020-05-14 Region Hovedstaden V/Herlev Hospital Ensemble électrode pour une distribution de champ électrique améliorée
JP2020517355A (ja) * 2017-04-28 2020-06-18 ファラパルス，インコーポレイテッド パルス電界アブレーションエネルギーを心内膜組織に送達するためのシステム、デバイス、および方法

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JP6893515B2 (ja) 2016-01-05 2021-06-23 ファラパルス，インコーポレイテッド 組織へのアブレーションエネルギーの送達のためのシステム、装置及び方法

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2010503496A (ja) * 2006-09-14 2010-02-04 ラジュール・テクノロジーズ・エルエルシイ 癌細胞を破壊する装置及び方法
JP2018515247A (ja) * 2015-05-12 2018-06-14 セント・ジュード・メディカル・エイトリアル・フィブリレーション・ディヴィジョン・インコーポレーテッド Ａｃ型心臓不可逆的電気穿孔法のための非対称形にバランスされた波形
JP2020517355A (ja) * 2017-04-28 2020-06-18 ファラパルス，インコーポレイテッド パルス電界アブレーションエネルギーを心内膜組織に送達するためのシステム、デバイス、および方法
WO2020094622A1 (fr) * 2018-11-05 2020-05-14 Region Hovedstaden V/Herlev Hospital Ensemble électrode pour une distribution de champ électrique améliorée

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JPWO2022176202A1 (fr) 2022-08-25

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